Apparatus and method for decreasing bio-effects of magnetic gradient field gradients

ABSTRACT

A magnetic field generator includes a power source and a coil connected to the power source to generate a time-varying magnetic field. Energy is applied to the coil so that the coil generates a time-varying magnetic field gradient with a magnitude of at least 1 milliTesla per meter and a rise-time of less than 10 microseconds. One or more of a capacitor, a multi-stage high-voltage switch, and/or a pulse-forming network may assist with the generation of the magnetic field gradient.

CROSS-REFERENCE TO RELATED APPLICATION(S)

This is a United States Non-Provisional Patent Application that relies for priority on U.S. Provisional Patent Application Ser. No. 61/074,397, filed on Jun. 20, 2008, the contents of which are incorporated herein by reference.

FIELD OF THE INVENTION

The present invention concerns an apparatus and a method for decreasing the bio-effects of magnetic field gradients on tissue(s). More specifically, the present invention concerns an apparatus and a method to decrease bio-effects on neurological tissue from magnetic field gradients, such as those experienced during Magnetic Resonance Imaging (“MRI”).

DESCRIPTION OF RELATED ART

As should be appreciated by those skilled in the art, MRI is a technology whereby a magnetic field gradient is applied to subatomic particles in tissue to spatially encode a subsequent response from the atoms and molecules in the tissue to a radiofrequency pulse. After detection of an electromagnetic response from the tissue, an image of the tissue is generated partly based on that response.

Unfortunately, the generation of magnetic field gradients (e.g., switching gradients) may elicit undesirable responses in a living organism by induction of electrical pulses in nerves and other electrically-sensitive tissues.

A model describing electromagnetic bio-effects was described by D R McNeal and J P Reilly in the mid to late 1970's (D R McNeal, “Analysis of a model for excitation of myelinated nerve,” in IEEE Trans. Biomed. Eng., 23:329-337, 1976; and J P Reilly, “Electric and Magnetic field coupling from high voltage AC power transmission lines—Classification of short-term effects on people,” in IEEE Trans. on Power Apparatus and Systems, 97(6): 2243-2252, 1978) based on classic membrane-excitability relations (A L Hodgkin and A F Huxley, “A quantitative description of membrane current and its application to conduction and excitation in nerve,” in J. Physiol., 117:500-544, 1952).

Subsequent elaborations of the model were disclosed by Reilly in “Sensory effects of transient electrical stimulation: Evaluation with a neuroelectric model,” IEEE Trans. Biomed. Eng., 32(12) 1001:1011, 1985.

The model elaborated by Reilly invokes the telegraph equation first applied in the late 1800's to design trans-Atlantic cables.

As in underwater cables, neurons are organized in sections that are separated by nodes of Ranvier. These nodes enforce resistance/capacitance (“RC”) equations that govern neuronal behavior, with time constants related to neuronal diameter and inter-nodal distances.

Having provided a brief overview of the electrical characteristics, attention is now turned to magnetic field gradients.

With respect to MRI, magnetic field gradients have at least one component of particular interest: the slew rate. The slew rate refers to the rate of change in the magnitude of the gradient, which is typically measured in Teslas per meter per second (T/m/s).

As the laws of physics dictate, changes in magnetic fields result in the generation of electrical fields. Changes in magnetic field gradients in tissue, therefore, also result in the formation of electric fields.

When studying neurological tissues, the changes in magnetic field gradients depolarize nerves, once a threshold is reached. This threshold becomes higher as the pulse duration becomes shorter. The relationship between these variables follows a traditional, hyperbolic curve.

It is noted that experimental studies in humans (D. J. Schaefer, J. D. Bourland, and J. A. Nyenhuis, “Review of Patient Safety in Time-Varying Gradient Fields,” in J. Magnetic Resonance Imaging, 12:20-29, 2000) have validated the basic model for pulse durations as short as fifty microseconds.

In response to various MRI studies, regulatory agencies have codified the strength-duration model into law, at least in Europe and the United States. (See Requirements for the Safety of MR Equipment for Medical Diagnosis, IEC 60601-2-33 (with respect to Europe); see also Guidelines for Premarket Notifications for MR Diagnostic Devices, 21 C.F.R. §807.87 (with respect to the US).)

As a result of these studies and as a result of the regulations that are based on these studies, MRI manufacturers have attempted to design triangular pulse sequences to conform to the limits prescribed by the Reilly model, among others.

One such attempt is described in U.S. Pat. No. 6,198,282, which is directed to an optimized gradient system for providing minimum-duration gradient pulses, the contents of which are incorporated herein by reference.

The prior art also includes evidence of interest in the strength-duration curve from another direction, as manufacturers of neuron-stimulators try to shape the pulse in order to increase stimulation. (See P. J. Maccabee, “Influence of pulse sequence, polarity and amplitude on magnetic stimulation of human and porcine peripheral nerve,” J. Physiol., 513:571-585, 1998).

As a result of numerous studies and advancements, those in the industry traditionally have applied magnetic field gradients less than a threshold for neuronal stimulation. As a result of the reduced gradient magnitude, the MRI diagnosis takes longer, and has reduced spatial resolution, than it would otherwise have with a higher magnetic gradient field strength.

There appears to be wide acceptance in the MRI community in the belief that the attainment of high gradient slew rates (i.e., the change in magnetic gradients over a short period of time) would be a welcome development for the industry.

As should be immediately apparent, one impetus for increasing slew rates is to reduce scan time. It is postulated that, if a given MRI sequence requires a certain number of pulses, then the application of shorter (but stronger) pulses, and of pulses with shorter ramp times, would permit the MRI sequence to be completed in a shorter time period (i.e., faster) than conventional techniques.

Among other benefits, saving time improves safety for unstable patients. Saving time also may reduce the cost of the MRI sequence.

A second incentive for increasing slew rate is to increase gradient field strength, which improves spatial resolution. For a given prescribed pulse sequence, the faster one can ramp up the magnetic field per pulse, the higher the gradient strength will be for the same overall scan time. Since the gradient strength is proportional to the spatial resolution of the MRI image obtained, a higher slew rate will result in a better spatial resolution. Increased spatial resolution may improve medical diagnosis in some cases.

As discussed above, for manufacturers of MRI devices, limits have been set for slew rates based on studies concerning the presence of bio-effects due to neuronal stimulation. These limits have placed a limit on currently-available scanning technologies.

As also should be appreciated by those skilled in the art, the generation of a magnetic field gradient with a very small duration presents technological challenges as well. Accordingly, there also has been a technological barrier to decreasing the duration of the magnetic field gradient pulses.

With respect to technological limitations, in some MRI devices, switches are used to trigger the generation of a magnetic field gradient. The types of switches traditionally used include Insulated-Gate Bipolar Transistor (“IGBT”) and Metal Oxide Semiconductor Field Effect Transistor (“MOSFET”)-based devices. However, these traditional switches are not capable of creating magnetic filed gradients with a sufficiently short duration to avoid neuronal stimulation.

Recent developments in switches offer a solution to the technological problem experienced with prior art MRI devices.

Specifically, several generations of plasma physics experimentalists have led the development of reliable solid-state switches and pulse-forming lines that are just now being introduced into the community. (See H. Sanders and S. Glidden, “High Power Solid State Switch Module,” in International Power Modulator Symposium Conference Record, pp. 563-566, 2004).

Those high-power solid-state switches are capable of triggering pulses of ten-thousand amps in one microsecond, orders of magnitude higher than the IGBT and MOSFET-based systems currently employed in commercial gradient field generators for MRI systems (See D. A. Seeber, J. H. Hoftiezer, and C. H. Pennington, “Pulsed current gradient power supply for microcoil magnetic resonance imaging,” in Magnetic Resonance Engineering, 15(3): 189-200, 2002).

It is axiomatic in the field of pulsed power technology that it is often easier to close a switch than to open a switch. To get around this limitation, solid-state switches may be combined with pulse-forming lines (“PFLs”), which do not require opening switches.

PFLs, which are also known as Blumlein lines (named for the World-War II-era inventor David Blumlein), are dielectric-filled transmission lines that begin draining their charge when triggered by a solid-state switch. The transmission lines stop delivering current once the dielectric has been drained of charge. Blumlein lines can switch in nanoseconds, and maintain currents for milliseconds. (K Gasthaus, “A millisecond Blumlein line for the power supply of a high power laser,” in J. Phys. E: Instrum., 20:192-195, 1987). In order to deliver pulses of varying widths, sets of PFLs may be triggered independently of one another into a common load.

In view of the foregoing, there exists a desire to apply higher magnetic field gradients to tissue in an MRI environment while avoiding adverse bio-effects on that tissue.

SUMMARY OF THE INVENTION

It is, therefore, one aspect of the present invention to provide an apparatus and a method for decreasing the duration of scan times for MRJ.

An additional aspect of the present invention involves the application of magnetic field gradients with a magnitude greater than that traditionally employed. In one embodiment, the gradient may be up to five (5) times greater than previously applied. In other embodiments, the magnitude may be greater.

It is another aspect of the present invention to decrease bio-effects from magnetic field gradients by applying a magnetic field gradient to tissue within a time frame below the response threshold for that tissue.

Among other things, the current invention takes advantage of a physiological loophole: according to accepted physiological models for ionic channel transport, bi-phasic pulses on the order of a microsecond are too fast for the nerve to change its polarization state, and are, therefore, effectively ignored. The present invention capitalizes on this physiological loophole.

According to the model elaborated by Reilly, this loophole implies that gradient field thresholds may be increased by factors of five or more above the usual hyperbolic model without triggering any bio-effects.

The present invention also takes advantage of magnetic pulse delivery systems that are more powerful than traditional systems used to deliver MRI pulses.

In one contemplated embodiment, the present invention utilizes solid-state switch and/or PFL technologies that conform to the requirements of MRI gradient amplifiers. These requirements include increased repetition rates, impedance and trigger matching to MRI pulse programming consoles, and electrical/acoustic noise shielding considerations. Downstream modifications include the buttressing of gradient coils to handle the higher electromagnetic (i.e., J×B) forces that will occur at higher current loads, especially in high resolution MRI systems with high static magnetic fields.

According to classic coil-design codes, eddy current shielding is likely to be less of a problem than at current regimes, and reductions in inductance are predicted. The influence of eddy currents may further be minimized by acquiring signals at long echo time (“TE”), when eddy currents have died down, as contemplated by still another embodiment of the present invention.

In one further contemplated embodiment, the bore of the cryostat may be made significantly larger than the gradient coil, further reducing the influence of eddy currents.

Other advantages of the present invention will be made apparent from the discussion that follows and will be appreciated by those skilled in the art.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention will now be described in connection with the drawings appended hereto, in which:

FIG. 1 is a schematic illustration of a first embodiment of an apparatus contemplated by the present invention;

FIG. 2 is a schematic illustration of a second embodiment of an apparatus contemplated by the present invention;

FIG. 3 is a schematic illustration of a third embodiment of an apparatus contemplated by the present invention;

FIG. 4 is a schematic illustration of a fourth embodiment of an apparatus contemplated by the present invention;

FIG. 5 is a flow chart illustrating one method contemplated by the present invention;

FIG. 6 is a graph depicting the magnetic field gradient and duration typical of a prior art MRI device as used clinically; and

FIG. 7 is a graph depicting the magnetic field gradient and duration contemplated by the present invention.

DESCRIPTION OF THE INVENTION

The present invention will now be described in connection with one or more embodiments. It is intended for the embodiments to be representative of the invention and not limiting of the scope of the invention. The invention is intended to encompass equivalents and variations, as should be appreciated by those skilled in the art.

As a prelude to the discussion of the various embodiments of the present invention, a general discussion of MRI devices is now provided. This overview is not intended to be limiting of the invention. It is provided merely to assist with an understanding of the components of the various embodiment of the present invention, as detailed below.

As a general rule, an MRI device includes a magnetic field generator, typically a magnetic coil and a radio frequency (“RF”) generator or transmitter. The magnetic coil generates a time-varying magnetic field and the RF generator emits radio waves. The MRI device typically also applies a static magnetic field.

As should be appreciated by those skilled in the art, tissue is primarily composed of water molecules, each of which contains hydrogen atoms. When a person's tissue is exposed to a strong magnetic field, the hydrogen atoms align with the direction of the magnetic field. Subsequently, the RF generator emits radio waves to the hydrogen atoms while in the aligned state. Some of the energy from the radio waves is absorbed by the hydrogen atoms in the water molecules, thereby altering the magnetic alignment of the hydrogen atoms. The altered magnetic state is detected by the detector, which generates signals that are processed to form as an image.

With this overview in mind, reference is now made to FIG. 1. FIG. 1 provides a schematic diagram of a first contemplated embodiment of a MRI device 10 according to the present invention.

The MRI device 10 includes a power source 12. The power source 12 may be any type of generator suitable for generating power to be provided to the one or more of the components connected thereto. The generator may provide an alternating current (AC) or a direct current (DC), as should be appreciated by those skilled in the art. The precise output of the power source 10 is not critical to the operation of the present invention. Moreover, the power output, once generated, may be converted different types (e.g., AC or DC) as required by individual components of the system.

In FIG. 1, the power source 12 is illustrated as providing power to each of the various components of the MRI device 10 of the present invention. It is noted, however, that the depicted arrangement is meant to be illustrative only. As should be appreciated by those skilled in the art, the individual components of the MRI device 10 may receive power from a centralized source, such as the power source 12. Alternatively, the various components may receive power from alternative power sources. Accordingly, the depiction of a single power source 12 is not intended to be limiting of the invention.

In addition, as detailed below, the MRI device 10 of the present invention is illustrated and discussed with reference to single communication lines (or links) extending between the various components. The illustration of single communication lines is meant to simplify the discussion and illustration of the various embodiments of the invention. As should be appreciated by those skilled in the art, there may be multiple communication lines between the various components of the MRI device 10 as required for their operation. Moreover, the communication lines are not intended to be limited to wired links. To the contrary, the communication lines may be wireless, as required or desired for operation of the MRI device 10.

In one contemplated embodiment of the present invention, the power source 12 may include a plurality of power sources 12, each of which generates power with different characteristics, as required by the device(s) and/or components associated therewith.

As depicted in FIG. 1, power from the power source 12 travels in two directions. Power from the power source 12 is conducted first along a communication line 14 to a capacitor 16. Power from the power source 12 is carried second along a communication line 18 to a processor 20.

The capacitor 16 may be of any size or type as would be appreciated by those skilled in the art. As is its nature, the capacitor 16 stores a charge based on the power inputted from the power source 12. That charge is eventually discharged, as discussed in greater detail below.

While FIG. 1 illustrates a single capacitor 16, a plurality of capacitors 16 may be employed without departing from the scope of the present invention. In one contemplated embodiment, the MRI device 10 relies upon a plurality of capacitors 16 for its operation. As should be appreciated by those skilled in the art, plural sets of capacitors 16 may be employed to generate successive magnetic field gradients.

In the second flow path, power from the power source 12 is provided to the processor 20. The processor 20 may be of any type suitable for executing instructions, generating data, receiving data, storing data, and the like. In one contemplated embodiment, the processor 12 may be a personal computer. In other embodiments, the processor 12 may be a mainframe computer, a portable computer, a personal data assistant (“PDA”) or any other similar device. The exact design and functionality of the processor 12 is not critical to operation of the present invention. Accordingly, the processor 12 may be of any type suitable for the operation of the MRI device 10.

The capacitor 16 is connected, via a communication line 22, to a switch, where the term switch refers to one or more high-power solid-state switch modules as described above. Accordingly, when the capacitor 16 discharges the stored charge, the stored charge passes through the communication line 22 to the switch 24.

The switch 24 is connected, via a communication line 26, to a coil 28. Accordingly, when the capacitor 16 is discharged, energy from the capacitor 16 is passed to the coil 28, which generates a magnetic field 30.

The coil 28 need not be a single coil. To the contrary, it is contemplated that the coil 28 may include a plurality of coils 28, each of which is capable of generating all or part of the magnetic field 30. Moreover, as should be appreciated by those skilled in the art, where plural coils 28 are employed, the coils 28 need not be of the same type or size. To the contrary, it is contemplated that, where plural coils 28 are employed, they may be differ from one another to produce magnetic field gradients of differing magnitudes, periods, etc.

As also shown in FIG. 1, the MRI device 10 includes an RF transmitter 32. As discussed briefly above, the RF transmitter 32 generates radio waves 34. While one RF transmitter 32 is illustrated, it is contemplated that a plurality of RF transmitters 32 may be employed without departing from the scope of the present invention. Moreover, where plural RF transmitters 32 are employed, they may be of different sizes, types, etc.

As illustrated, the magnetic field 30 and the RF waves 34 are directed at a tissue sample 36. While the tissue sample 36 may be a portion of an organism, it may also be a complete organism.

After interaction of the magnetic field 30 and the RF waves 34 with the tissue 36, the tissue 36 generates a responsive signal 38 that is detected by the detector 40. As should be appreciated by those skilled in the art, the signal 38 may encompass a multitude of different signals from the tissue 36. The detector 40 detects the signals 38 and passes the signals 38 to the processor 20 via the communication line 42. The processor 20 receives and processes the signals 38 to generate an image representative of the composition of the tissue 36.

As should be appreciated by those skilled in the art, the processor 20 may not be the device that processes the signals 38 to generate the image of the tissue 36. To the contrary, the detector 40 may be combined with a suitable imaging device. In still another embodiment, the imager may be a component separate from the processor 20 and the detector 40. Still further embodiments are contemplated to fall within the scope of the present invention.

With continued reference to FIG. 1, the MRI device 10 includes communication line 42. Communication line 42 is illustrated as a central bus that connects the processor 20 to the capacitor via communication line 44, to the switch, via communication line 46, to the coil, via communication line 48, and to the RF transmitter, via communication line 50. A central bus, however, is not required to practice the invention. To the contrary, multiple connections may be established between the components of the MRI device 10 without departing from the scope of the invention, as discussed above.

It is noted that the communication lines 14, 18, 22, 26, 42, 44, 46, 48, 50 all may conduct data and/or power. The communication lines, therefore, are meant to illustrate multi-modal connections between the various components of the MRI device 10. As noted above, each of the communication lines 14, 18, 22, 26, 42, 44, 46, 48, 50 may be replaced with one or more separate connections, as required or desired. The communication lines 14, 18, 22, 26, 42, 44, 46, 48, 50 may be unidirectional or bidirectional as required or desired.

With respect to the communication lines 42, 44, 46, 38, 50, it is contemplated that the processor 20 will provide operating instructions to one or more of the components to which it is connected. The processor 20, therefore, is contemplated to incorporate control functionality over one or more of the components, as should be appreciated by those skilled in the art. It is also contemplated that controls may be fed from one component to another, as required or desired for operation of the MRI device 10.

FIG. 2 illustrates an MRI device 52, which is a second embodiment contemplated by the present invention. Many of the components of the MRI device 52 are the same as illustrated and described in connection with MRI device 10 in FIG. 1. As a result, those components are provided with the same reference numbers as the components in FIG. 1. Moreover, the descriptions of these components is not repeated for the sake of brevity.

The MRI device in FIG. 2 differs from the MRI device 10 in FIG. 1 in at least one respect. Specifically, the capacitor 16 and the switch 24 have been replaced with a pulse-forming line 54. As should be appreciated by those skilled in the art, the pulse-forming line 54 may include one or more capacitors and switches. The pulse forming line 54 is connected to the power source 12 via communication line 56. The pulse forming line 54 is connected to the coil 28 via the communication line 58. The pulse forming line 54 connects to the processor via the communication line 60.

As discussed above, a pulse forming line 54 is also known as a Blumlein line. Pulse forming lines 54 are transmission lines that begin draining their charge in response to a triggering event, such as when triggered by a solid-state switch. Pulse forming lines 54 also are referred to as pulse forming networks. A pulse forming network (“PFN”) accumulates electrical energy over a predetermined period of time and releases the electrical energy in the form of a square pulse in a relatively short period of time, depending upon the materials that make up the PFN 54. PFNs 54 also may be engineered to provide pulsed power. A PFN 54 may be charged by a high voltage power source 12 and then rapidly discharged (possibly via a high voltage switch).

The pulse forming line 54 may be a single line or may be a plurality of lines combined together. The pulse forming line 54 also may be a pulse forming network 54, as discussed above. The exact composition and construction of the PFN 54 is not critical to operation of the present invention.

FIG. 3 illustrates a third embodiment of an MRI device 62. This embodiment is similar to the MRI device 52 illustrated in FIG. 2. In this third embodiment, however, a switch 64 has been added between the power source 12 and the pulse forming line 54. As illustrated, the power source is connected to the switch via a communication line 66. The switch 65, in turn, is connected to the processor 20 via the communication line 68. As noted above, the switch 65 may be employed to trigger the pulse forming line 54 to release its energy to the coil 28.

FIG. 4 illustrates a fourth embodiment of an MRI device 70. This fourth embodiment is a modification of the MRI device 62, which is illustrated in FIG. 3. Here, a capacitor 72 has been inserted between the switch 64 and the power source 12. The capacitor 72 connects to the power source via the communication line 74. The capacitor 72 connects to the processor via the communication line 76. In this embodiment, it is contemplated that the capacitor 72 will discharge power to the switch 64, which will discharge power through the pulse forming line 54 to the coil 28, as illustrated.

With respect to the embodiments illustrated in FIGS. 1, 2, 3, and 4, and for purposes of the present invention, the connection between the power source 12 and the coil 28 is considered to be a controlled communication line. As a result, the embodiments provide variations for contemplated constructions of that controlled communication line.

FIG. 5 illustrates a method 78 contemplated by the present invention. The method 78 starts at 80 and ends at 88. Following the start 80, at 82, a magnetic field gradient with a minimum amplitude of 1 milliTesla per meter (mT/m) is generated. At 84, the magnetic field gradient is maintained for a least about 1 microsecond and up to about 10 milliseconds (this is the plateau time period, as discussed below). At 86, the magnetic field gradient is changed in a time frame small enough to fail to solicit a response from neurological tissue. A decision point 85 follows the operation identified at 86. As the flow chart in FIG. 5 indicates, via the decision point 85, steps 84 and 86 are repeated as necessary to obtain physiological and/or anatomic information about tissues. If the pulse sequence is sufficient to obtain the necessary physiological and/or anatomic information about tissues, then the method 78 ends at 88.

As discussed in greater detail below, it is contemplated that application of the magnetic field gradient with rise- and fall-times of less than about 10 microseconds will establish suitable conditions to avoid triggering a biological response from neurological tissue. As should be appreciated by those skilled in the art, and as discussed in greater detail below, the present invention permits the application of a magnetic field gradient higher than that permitted using existing technology, because the present invention relies, at least in part on shorter rise- and fall-times than available in the prior art.

FIG. 6 is a graphical illustration of a single magnetic field gradient pulse according to the prior art. The rise-time t_(rise) (approximately 150 microseconds) and fall-time t_(fall) (approximately 150 microseconds) of the magnetic field gradient pulse exceed a neurological response time t_(response) for neurological tissue at a typical magnetic field slew rate S_(typical). For a typical clinical system, S_(typical) is 400 T/m/s. Data acquisition is typically performed during the plateau phase, because of difficulties in deconvolving the effects of the changing gradient field. As a result, the most useful portion of the pulse is the plateau time, t_(plateau). The pulse duration includes both the rise and fall times as well as the plateau time, for a typical total duration of 500 microseconds. It should, therefore, be apparent that shortening the rise and fall times can reduce overall scan time.

As should be appreciated by those skilled in the art, the terms “rise” and “fall” may be applied to both negative- and positive-generated pulses.

FIG. 7 provides a graphical illustration of a magnetic field gradient pulse generated according to the present invention. The shortened pulse rise-time duration t_(short) _(—) _(rise) is less than the rise-time t_(rise) according the practice in the prior art. The current invention typically would employ a t_(short) _(—) _(rise) of 10 microseconds or less. The shortened pulse fall-time duration t_(short) _(—) _(fall) is less than the fall-time t_(fall) according the practice in the prior art. The current invention typically would employ a t_(short) _(—) _(fall) of 10 microseconds or less. Also, the pulse ramp times t_(short) _(—) _(rise and t) _(short) _(—) _(fall) are less than the neurological response time t_(response) for neurological tissue at a typical magnetic field slew rate S_(typical). The slew rate in the present invention is increased as a result of the reduced pulse ramp times. In the present invention, the plateau magnitude is increased, as compared to the prior art, because of several factors. Firstly, the plateau magnitude may be increased because of the improved switching techniques as described above. Secondly, the plateau magnitude may be increased because the tissues are depolarized and repolarized within a short period of time similar to to the neurological response time t_(response), in a multi-phasic train of pulses as prescribed by the model according to Reilly.

As should be apparent, the short duration of the time periods t_(short) _(—) _(rise) and t_(short) _(—) _(fall) make possible the application of a large magnitude magnetic pulse without soliciting a biological response from neurological tissue. As discussed above, it is the change in the magnetic field that elicits a biological response. With a rapid change in magnetic field strength, the effects on the biological tissue may be minimized such that there is little or no biological response from the tissue.

It is contemplated that the magnitude of the pulse during the time period t_(plateau) may be any value. As discussed above, the magnitude may be as small as 1 mT/m. It is contemplated that the magnitude may be smaller or greater than 1 mT/m, as required or desired for a particular application. While the magnitude of the magnetic field is theoretically unbounded at its upper limit, it is foreseeable that the magnitude may be 1000 mT/m or less.

As for the duration of the time periods t_(short) _(—) _(rise) and t_(short) _(—) _(fall), it is contemplated that these time periods will fall in a range between about 1 and about 10 microseconds. As noted above, 10 microseconds is a sufficiently short time period in which to change a magnetic field so that tissue does not react biologically. Naturally, the shorter the duration of t_(short) _(—) _(rise) and t_(short) _(—) _(fall), the smaller the likelihood of eliciting a biological response. In keeping with this premise, it is contemplated that the invention will operate with one or both of the time periods, t_(short) _(—) _(rise) and t_(short) _(—) _(fall), being less than about 9 microseconds. In another contemplated embodiment, one or both of the time periods is less than about 8 microseconds. In still another contemplated embodiment, one or both of the time periods is less than about 7 microseconds. Further, the time periods are less than about 6 microseconds in another contemplated embodiment. In one other contemplated embodiment, one or both of the time periods is less than about 5 microseconds. One or both of the time periods may be less than about 4 microseconds in yet another contemplated embodiment. Still further, it is contemplated that one or both of the time periods is less about than 3 microseconds. In an additional contemplated embodiment, one or both time periods is less than about 2 microseconds. In one further contemplated embodiment, one or both of the time periods is less than about 1 microsecond. As should be apparent, the time periods, t_(short) _(—) _(rise) and t_(short) _(—) _(fall), need not be identical in duration. The variable t_(short) _(—) _(rise) may be greater than, equal to, or less than the variable t_(short) _(—) _(fall) without departing from the scope of the present invention.

In the present invention, the shortening of overall scan times is effected through at least mechanisms in the present invention: Firstly, the reduced rise- and fall-times lead to an overall reduction in scan time. Secondly, the higher plateau magnitude allows the MRI system to acquire data of quality comparable to the prior art using a shorter plateau time t_(short) _(—) _(plateau).

A comparison between FIGS. 6 and 7 also illustrate one further aspect of the present invention. Specifically, the magnetic field gradient as generated by the prior art is about 5 times weaker than the magnetic field gradient generated by the MRI device 10 of the present invention.

In summary, the invention consists of an apparatus to deliver very short multi-phasic magnetic gradient pulses for magnetic resonance imaging. The invention also includes the method of decreasing bio-effects in magnetic resonance imaging through the use of reduced pulse lengths and multi-phasic magnetic gradient pulses.

As discussed, the magnetic pulses are created by releasing electrical charge stored in capacitors and/or transmission lines into coils and/or transmission lines near a body part. The coils may include dielectric and/or ferrite materials which assist in the shaping of the magnetic pulses. Ferrite materials may be used to construct complex dynamic electromagnetic fields for circulators and other circuit elements employed in microwave transmission and receivers (as disclosed by Ansoft Corporation, in Microwave Journal, June, 1996).

Among other differences, the invention differs from the prior art by prescribing multi-phasic pulse trains within a short period of time similar to the neurological response time t_(response), unlike the pulse sequences previously taught.

Other aspects of the present invention should be apparent to those skilled in the art based on the discussion provided herein. 

1. A magnetic field generator for magnetic resonance imaging, comprising: at least one power source; at least one capacitor; at least one multi-stage high-voltage switch; at least one coil to generate a time-varying magnetic field; wherein the stored energy from the at least one capacitor is delivered through the at least one multi-stage high-voltage switch to the at least one coil, so that the at least one coil generates a time-varying magnetic field gradient with a magnitude of at least 1 milliTesla per meter and a rise-time of less than 10 microseconds.
 2. The generator of claim 1, wherein the at least one coil comprises a ferrite material.
 3. A magnetic field generator for magnetic resonance imaging, comprising: at least one power source; at least one switch; at least one pulse-forming line; at least one coil to generate a time-varying magnetic field; wherein the stored energy from the at least one pulse-forming line is delivered to the at least one coil.
 4. A method of implementing magnetic resonance imaging of structures containing neurologic tissue, comprising: generating a magnetic field gradient with a minimum magnitude of at least 1 milliTesla per meter in such a small time duration as to fail to solicit a response from neurological tissue exposed thereto; and maintaining the magnetic field at a magnitude of at least 1 milliTesla per meter for a period of time of at least one microsecond; and changing the magnitude of the magnetic field gradient in such a small time duration as to fail to solicit a response from neurological tissue exposed thereto.
 5. The method of claim 4, wherein the neurological tissue comprises at least a portion of a living organism.
 6. The method of claim 4, where the neurological tissue comprises at least one neuron.
 7. The method of claim 4, wherein the magnetic field is generated using a magnetic field generator for magnetic resonance imaging that comprises at lease one power source, at least one coil connected to the at least one power source to generate a time-varying magnetic field, at least one capacitor connected to the coil, wherein the at least one capacitor stores energy from the at least one power source that is applied to the at least one coil, and at least one multi-stage high-voltage switch connected between the capacitor and the coil, wherein the stored energy from the capacitor is delivered to the at least one coil so that the coil generates the magnetic field gradient.
 8. The method of claim 4, wherein the magnetic field is generated using a magnetic field generator for magnetic resonance imaging that comprises at least one power source, at least one coil connected to the at least one power source to generate a time-varying magnetic field, and at least one pulse-forming network connected between the at least one power source and the at least one coil, wherein the stored energy from the at least one pulse-forming network is delivered to the at least one coil so that the coil generates the magnetic field gradient. 